Clot retrieval device for removing clot from a blood vessel

ABSTRACT

A clot removal device including a first scaffolding section, a second scaffolding section distal of the first scaffolding section by a first hinged element including a pinching cell. The pinching cell has a collapsed state and an expanded state configured to pinch at least a portion of a clot. A third scaffolding section is distal of the second scaffolding section by a second hinged strut element including a pinching cell that has a collapsed state and an expanded state configured to pinch at least a portion of the clot. An outer diameter of the third scaffolding section is greater than an outer diameter of the second scaffolding section, which is greater than an outer diameter of the first scaffolding section.

FIELD

The present disclosure generally relates to devices and methods for removing blockages from blood vessels during intravascular medical treatments.

BACKGROUND

Clot retrieval devices are used in mechanical thrombectomy for endovascular intervention, often in cases where patients are suffering from conditions such as acute ischemic stroke (AIS), myocardial infarction (MI), and pulmonary embolism (PE). Acute obstructions may include clot, misplaced devices, migrated devices, large emboli and the like. Thromboembolism occurs when part or all of a thrombus breaks away from the blood vessel wall. This clot (now called an embolus) is then carried in the direction of blood flow. An ischemic stroke may result if the clot lodges in the cerebral vasculature. A pulmonary embolism may result if the clot originates in the venous system or in the right side of the heart and lodges in a pulmonary artery or branch thereof. Clots may also develop and block vessels locally without being released in the form of an embolus—this mechanism is common in the formation of coronary blockages. There are significant challenges associated with designing clot removal devices that can deliver high levels of performance. First, there are a number of access challenges that make it difficult to deliver devices. In cases where access involves navigating the aortic arch (such as coronary or cerebral blockages) the configuration of the arch in some patients makes it difficult to position a guide catheter. These difficult arch configurations are classified as either type 2 or type 3 aortic arches with type 3 arches presenting the most difficulty.

The tortuosity challenge is even more severe in the arteries approaching the brain. For example it is not unusual at the distal end of the internal carotid artery that the device will have to navigate a vessel segment with a 180° bend, a 90° bend and a 360° bend in quick succession over a few centimetres of vessel. In the case of pulmonary embolisms, access is through the venous system and then through the right atrium and ventricle of the heart. The right ventricular outflow tract and pulmonary arteries are delicate vessels that can easily be damaged by inflexible or high profile devices. For these reasons it is desirable that the clot retrieval device be compatible with as low profile and flexible a guide catheter as possible.

Second, the vasculature in the area in which the clot may be lodged is often fragile and delicate. For example neurovascular vessels are more fragile than similarly sized vessels in other parts of the body and are in a soft tissue bed. Excessive tensile forces applied on these vessels could result in perforations and hemorrhage. Pulmonary vessels are larger than those of the cerebral vasculature, but are also delicate in nature, particularly those more distal vessels.

Third, the clot may comprise any of a range of morphologies and consistencies. For example, clot can be difficult to grip and improper grip can lead to fragmentation which may cause embolization. Long strands of softer clot material may also tend to lodge at bifurcations or trifurcations, resulting in multiple vessels being simultaneously occluded over significant lengths. More mature and organized clot material is likely to be less compressible than softer fresher clot, and under the action of blood pressure it may distend the compliant vessel in which it is lodged. Furthermore the inventors have discovered that the properties of the clot may be significantly changed by the action of the devices interacting with it. In particular, compression of a blood clot causes dehydration of the clot and results in a dramatic increase in both clot stiffness and coefficient of friction.

The challenges described above need to be overcome for any devices to provide a high level of success in removing clot and restoring flow. Existing devices do not adequately address these challenges, particularly those challenges associated with vessel trauma and clot properties.

SUMMARY

It is an object of the present design to provide devices and methods to meet the above-stated needs. It is therefore desirable for a clot retrieval device to remove clot from cerebral arteries in patients suffering AIS, from coronary native or graft vessels in patients suffering from MI, and from pulmonary arteries in patients suffering from PE and from other peripheral arterial and venous vessels in which clot is causing an occlusion.

In some examples, the device includes pinch features along at the site of an occlusion (e.g., in the mid internal carotid artery (ICA)). The device can be configured to reperfuse a vessel and/or remove a clot that has a fibrin core. In some examples, the fibrin core can be in a mid- or distal-position in the clot surrounded by relatively soft thrombus.

In some examples, the device is configured to remove a clot in the M1 bifurcation.

In some examples, the device is configured to remove a clot in the M2 bifurcation.

In some examples, the device includes a first scaffolding section; a second scaffolding section distal of the first scaffolding section by a first hinged element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of a clot; a third scaffolding section distal of the second scaffolding section by a second hinged strut element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of the clot; and an outer diameter of the third scaffolding section being greater than an outer diameter of the second scaffolding section which is greater than an outer diameter of the first scaffolding section.

In some examples, each scaffolding section includes a plurality of struts that form an array of closed cells.

In some examples, the device includes a hinged element with a pinching cell proximal of the first scaffolding section and connected to a distal end of a shaft.

In some examples, each pinching cell has at least one of an eyelet, a notched element to embed with clot, or a sinusoidal strut pattern.

In some examples, the first scaffolding section is extended at least partially over an inner body including a flow channel configured to engage the clot and restore blood flow through the clot, the inner body including a collapsed state and an expanded state. The outer diameters of the first scaffolding section and second scaffolding section is greater than an outer diameter of the inner body in the deployed configuration to define a clot reception space between the inner body and the separate first and second scaffolding sections. The device further includes a first clot inlet mouth between the first and second scaffolding section. In some examples, each hinged element is configured to self-align the corresponding scaffolding sections to articulate in bends of the vasculature.

In some examples, the first scaffolding section is eccentrically coupled over the inner body. In some examples, the second scaffolding section is extended at least partially over an inner body including a flow channel configured to engage the clot and restore blood flow through the clot, the inner body of the second scaffolding section includes a collapsed state and an expanded state. Each hinge can be being the only point of contact between respective clot scaffolding sections.

In some examples, a proximal end of each respective flow channel is joined at a respective proximal end of a respective scaffolding section and a distal end of each respective flow channel joined at a respective subsequent scaffolding section.

In some examples, a second clot inlet mouth is positioned between the second scaffolding section and the third scaffolding section.

In some examples, each of the first, second, and third scaffolding sections includes an open distal end.

In some examples, each of the first, second, and third scaffolding sections includes a closed proximal end.

In some examples, each of the first, second, and third scaffolding sections comprise a plurality struts formed of closed cells, the distal end of at least one of the first, second, and third scaffolding sections terminates in at least one distal apex free from connection to an adjacent closed cell of the respective scaffolding sections.

In some examples, the at least one distal apex is a petal or leaf member configured to open up in a flower-like manner and expand in one or more bifurcations of the vasculature to remove the clot.

In some examples, closed cells of the first scaffolding section are smaller than cells of the second scaffolding section.

In some examples, closed cells of the second scaffolding section are smaller than cells of the third scaffolding section.

In some examples, each of the first, second, and third scaffolding sections proximally taper from an open distal end to a closed proximal end.

In some examples, each of the first, second, and third scaffolding sections includes a plurality struts formed of closed cells, the distal end of at least one of the first, second, and third scaffolding sections terminates in crowns with no distal connecting elements. At least one of the crowns is configured to pivot open in a flower-like manner as clot engages therewith.

In some examples, expanding the clot removal device causes that at least one of pinching cells, the first scaffolding section, the second scaffolding section, and the third scaffolding section to deform at least a portion of the clot.

In some examples, each pinching cell includes a plurality of bowed strut members configured to actuate and pinch the clot from a blood vessel between the pair of bowed strut members. In some examples, the strut members form a network of struts operable to engage and then pinch at least a portion of a clot. In some examples, the bowed strut members being positioned about one or more central strut members, each strut member joined at common respective proximal and distal ends. In some examples, each of the pinching cells is configured to pinch the clot on movement from the collapsed state to a clot pinching state of the expanded state until a portion of the clot is compressed between a respective pinching cell. In some examples, a ratio of a diameter of each pinching cell between the collapsed state and expanded state is from approximately 1.5:1 to 4:1.

In some examples, the third scaffolding section includes a constrained delivery configuration and an at least partially constrained clot pinching configuration, at least a portion of the third scaffolding section being configured to engage clot in the expanded state and to pinch clot on movement from the expanded state to the clot pinching configuration.

In some examples, the third scaffolding section includes a clot pinching structure configured to pinch clot on movement from the expanded state to the clot pinching configuration.

In some examples, the clot pinching structure includes a spiral form.

In some examples, the clot pinching structure includes a non-tubular planar form.

In some examples, the third scaffolding section includes a longitudinal axis and the clot pinching structure extends around the longitudinal axis in a spiral.

In some examples, the third scaffolding section is configured to exert an outward radial force when deployed within a lumen whose inner diameter is lower than that of the expanded state. In some examples, the outward radial force can vary in a generally sinusoidal pattern along a length of the third scaffolding section, the generally sinusoidal pattern including a wave pattern and the amplitude generally consistent along the length. In some examples, the outward radial force can vary in a generally sinusoidal pattern along a length of the third scaffolding section, the generally sinusoidal pattern including a wave pattern and the amplitude generally decreasing along the length being higher at a proximal end of the third scaffolding section and lower at the distal end of the third scaffolding section.

In some examples, at least five (5) pinching cells are positioned end-to-end between proximal and distal ends of device.

In some examples, at least three (3) pinching cells are positioned end-to-end between proximal and distal ends of device.

In some examples, a clot removal device is disclosed including a first scaffolding section; a second scaffolding section distal of the first scaffolding section by a first hinged element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of a clot; and a third scaffolding section distal of the second scaffolding section by a second hinged strut element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of a clot.

In some examples, a method for removing a clot is disclosed. The method includes delivering a clot removal device in a blood vessel at or adjacent a site of a clot, the clot removal device including a collapsed state and an expanded state and including a first scaffolding section, a second scaffolding section distal of the first scaffolding section by a first hinged element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of a clot; a third scaffolding section distal of the second scaffolding section by a second hinged strut element including a pinching cell including a collapsed state and an expanded state configured to pinch at least a portion of a clot. The method includes embedding at least one of cells and scaffolding sections with at least a portion of the clot in a clot reception space by expanding the clot removal device from the collapsed state to the expanded state; and removing at least a portion of the clot by withdrawing the clot removal device.

In some examples, an outer diameter of the third scaffolding section is greater than an outer diameter of the second scaffolding section which is greater than an outer diameter of the first scaffolding section.

In some examples, an outer diameter of the third scaffolding section being approximately equal to an outer diameter of the second scaffolding section which is approximately equal to an outer diameter of the first scaffolding section.

In some examples, the method includes sequentially positioning at least five (5) pinching cells end-to-end.

In some examples, the method includes sequentially positioning at least three (3) pinching cells end-to-end.

In some examples, the step of embedding further includes expanding at least one of the first, second, and third scaffolding sections and urging at least the portion of the clot in the clot reception space.

In some examples, the method includes resheathing a microcatheter at least partially over the device to grip, pinch, and/or tweeze, by at least one of the cells or section, the clot.

In some examples, the method includes capturing at least some of the clot using the first scaffolding section.

In some examples, the method includes capturing at least some of the clot using the second scaffolding section.

In some examples, the method includes capturing at least some of the clot using the third scaffolding section.

In some examples, the method includes pinching, gripping, and/or tweezing at least some of the clot using at least one of the one or more pinching cells.

In some examples, the method includes expanding the clot removal device so that the scaffolding sections deform at least a portion of the clot between an inlet between the first and second scaffolding sections and/or between the second and third scaffolding sections.

In some examples, the third scaffolding section includes a constrained delivery configuration and an at least partially constrained clot pinching configuration, the method including engaging and pinching clot, by at least a portion of the third scaffolding section, on movement from the expanded state to the clot pinching configuration.

In some examples, the method includes exerting an outward radial force, by the third scaffolding section, when deployed within a lumen whose inner diameter is lower than that of the expanded state.

In some examples, the method includes varying the outward radial force in a generally sinusoidal pattern along a length of the third scaffolding section, the generally sinusoidal pattern including a wave pattern and the amplitude generally consistent along the length.

In some examples, the method includes varying the outward radial force in a generally sinusoidal pattern along a length of the third scaffolding section, the generally sinusoidal pattern including a wave pattern and the amplitude generally decreasing along the length being higher at a proximal end of the third scaffolding section and lower at a distal end of the third scaffolding section.

In some examples, the method includes terminating a distal end of at least one of the first, second, and third scaffolding sections in at least one distal apex free from connection to an adjacent closed cell of the respective scaffolding sections.

In some examples, the method includes opening up the at least one distal apex in a flower-like manner in the expanded state; and expand the at least one distal apex in one or more bifurcations of the vasculature to remove the clot, the at least one distal apex being a petal or leaf member hingedly connected to at least one strut of the respective scaffolding sections.

In some examples, the method includes extending the first scaffolding section at least partially over an inner body including a flow channel configured to engage the clot and restore blood flow through the clot, the inner body including a collapsed state and an expanded state; the outer diameters of the first scaffolding section and second scaffolding section being greater than an outer diameter of the inner body in the deployed configuration to define a clot reception space between the inner body and the separate first and second scaffolding sections, the device further including a first clot inlet mouth between the first and second scaffolding section.

In some examples, the method includes each hinged element self-aligning the corresponding scaffolding sections to articulate in bends of the vasculature.

In some examples, the method includes eccentrically coupling the first scaffolding section over the inner body.

Other aspects and features of the present disclosure will become apparent to those of ordinary skill in the art, upon reviewing the following detailed description in conjunction with the accompanying figures.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and further aspects of this disclosure are further discussed with the following description of the accompanying drawings, in which like numerals indicate like structural elements and features in various figures. The drawings are not necessarily to scale, emphasis instead being placed upon illustrating principles of the disclosure. The figures depict one or more implementations of the inventive devices, by way of example only, not by way of limitation. It is expected that those of skill in the art can conceive of and combining elements from multiple figures to better suit the needs of the user.

FIG. 1 illustrates a side view of a clot retrieval device of this disclosure.

FIG. 2A depicts a close-up view of an example pinching cell.

FIG. 2B depicts a close-up view of an example pinching cell.

FIG. 2C depicts a close-up view of an example pinching cell.

FIG. 3A depicts a close-up view of an example pinching cell.

FIG. 3B depicts a close-up view of an example pinching cell.

FIG. 4 depicts a side view of an example clot retrieval device of this disclosure in an example blood vessel in use with an example clot.

FIG. 5A depicts a side view of the example clot retrieval device of FIG. 4 in an example blood vessel in use with an example clot.

FIG. 5B depicts a side view of the example clot retrieval device of FIG. 4 in an example blood vessel in use with an example clot.

FIG. 6A depicts a side view of another example clot retrieval device in an example blood vessel in use with an example clot.

FIG. 6B depicts a side view of the example clot retrieval device of FIG. 6A in the example blood vessel in use with the example clot at the M1/M2 bifurcation.

FIG. 7A depicts a side view of another example clot retrieval device.

FIG. 7B depicts a side view of another example clot retrieval device.

FIG. 8 is a flow diagram illustrating a method of removing a clot from a blood vessel of a patient, according to aspects of the present disclosure.

DETAILED DESCRIPTION

Specific examples of the present disclosure are now described in detail with reference to the Figures, where identical reference numbers indicate elements which are functionally similar or identical. The examples address many of the deficiencies associated with traditional catheters, such as inefficient clot removal and inaccurate deployment of catheters to a target site.

Accessing the various vessels within the vascular, whether they are coronary, pulmonary, or cerebral, involves well-known procedural steps and the use of a number of conventional, commercially-available accessory products. These products, such as angiographic materials and guidewires are widely used in laboratory and medical procedures. When these products are employed in conjunction with the system and methods of this disclosure in the description below, their function and exact constitution are not described in detail.

The following detailed description is merely exemplary in nature and is not intended to limit the disclosure or the application and uses of the disclosure. Although the description of the disclosure is in many cases in the context of treatment of intracranial arteries, the disclosure may also be used in other body passageways as previously described.

It will be apparent from the foregoing description that, while particular embodiments of the present disclosure have been illustrated and described, various modifications can be made without departing from the spirit and scope of the disclosure. For example, while the embodiments described herein refer to particular features, the disclosure includes embodiments having different combinations of features. The disclosure also includes embodiments that do not include all of the specific features described. Specific embodiments of the present disclosure are now described in detail with reference to the figures, wherein identical reference numbers indicate identical or functionality similar elements. The terms “distal” or “proximal” are used in the following description with respect to a position or direction relative to the treating physician. “Distal” or “distally” are a position distant from or in a direction away from the physician. “Proximal” or “proximally” or “proximate” are a position near or in a direction toward the physician.

Accessing cerebral, coronary and pulmonary vessels involves the use of a number of commercially available products and conventional procedural steps. Access products such as guidewires, guide catheters, angiographic catheters and microcatheters are described elsewhere and are regularly used in catheter lab procedures. It is assumed in the descriptions below that these products and methods are employed in conjunction with the device and methods of this disclosure and do not need to be described in detail.

The following detailed description is merely exemplary in nature and is not intended to limit the disclosure or the application and uses of the disclosure. Although the description of the disclosure is in many cases in the context of treatment of intracranial arteries, the disclosure may also be used in other body passageways as previously described.

A common theme across many of the disclosed designs is a multi-layer construction in which the device in certain instances can include an outer expandable member within which, at times, can include an inner expandable member, both members being directly or indirectly connected to an elongate shaft. Turning to FIG. 1 , one example device 100 according to this disclosure is illustrated. In particular, device 100 is shown in a side view whereby a proximal end 104 of device 100 is connected to distal end of an elongate shaft 106. As shown, the distal end of shaft 106 extends interior of the artery and a proximal end that extends exterior of the artery. Device 100 can include a plurality of pinching cells 150, including a first cell 150 at or adjacent proximal end 104 and connected to shaft 106. The first cell 150 can be integral with shaft 106 or separate. The first pinching cell 150 can be connected to a first scaffolding section 110 and be configured to embed and grip, pinch, and/or “tweeze” the clot, as shown and described more particularly in FIGS. 2A-3B. As discussed herein, the term “tweeze” or “tweezing” is intended to refer to the sheathing of the pinching or squeezing cells (e.g., close cells of section 130 or cells 150 themselves) that causes respective struts to come together and tweeze or grip at least a portion of clot. In this respect, while the numbers of struts in a respective cell need not be limited, at least two strut surfaces must be included so as to tweeze corresponding clot material.

Shaft 106 can be a tapered wire shaft, and may be made of stainless steel, MP35N, Nitinol or other material of a suitably high modulus and tensile strength. Shaft 106 can also have indicator one or more bands proximal of the patient to indicate to the user when the distal end of the device 100 is approaching the end of the microcatheter during insertion.

Section 110 can include a collapsed configuration for delivery and an expanded configuration for clot retrieval, flow restoration and/or fragmentation protection. To move between the delivery to the expanded configurations, section 110 is configured to self-expand upon delivery from the microcatheter (e.g., release from the microcatheter) to a diameter larger than that of member 103. Section 110 can include an outer expandable body with an inner expandable member 103 with a generally tubular inner flow channel, to facilitate restoration of blood flow through clot immediately after the clot retrieval device 100 is deployed at an obstructive site. Expansion of the outer expandable body of section 110 can cause compression and/or displacement of the clot during expansion. The inner channel of member 103 may also comprise a portion that compresses an area of the clot in order to form a blood communication channel across the clot C. Such a channel can serve to reduce the pressure gradient across clot C, thus reducing one of the forces that must be overcome in order to retract the clot C. The flow channel of member 103 can also a flow path for oxygenated, nutrient carrying blood to reach the ischemic area distal of the clot.

The outer, expandable body of section 110 can provide a high level of scaffolding that provides an escape path or opening to urge the clot towards the opening or clot inlet 115. When inlet openings 115, in the outer expandable body of section 110 and/or between the outer expandable body and member 103, these inlet openings 115 provide the primary movement freedom available to the clot and so the expansion of section 110 urges the clot into a reception space defined between member 103, the outer expandable body and any clot scaffolding section(s) distal thereof. Inlet(s) 115 are configured to allow portions of the clot to enter the reception space between the respective outer expandable body of section 110 and member 103, and thus allow the clot to be retrieved without being excessively compressed.

This is advantageous because compression of clot causes it to dehydrate, which in turn increases the frictional properties of the clot, and increases its stiffness, all of which makes the clot more difficult to disengage and remove from the vessel. This compression can be avoided if the clot migrates inward through the outer wall of section 110 as the porous structure migrates outward towards the vessel wall. In some examples, the struts of sections 110, 120, and/or 130 include a relatively low coefficient of friction through polishing, hydrophilic coating, PTFE coating, silicon lubricant or the like so that the clot can easily slide off these segments and through corresponding inlet(s) 116 and into the reception space.

As shown, device 100 can include second scaffolding section 120 and third scaffolding section 130, each including outer expandable bodies similar structurally to that of section 110. However, an outer diameter of section 130 can be greater than an outer diameter of section 120, which can be greater than an outer diameter of section 110. Sections 110, 120, 130 are preferably made of a super-elastic or pseudo-elastic material (e.g., Nitinol or another such memory alloy with a high recoverable strain).

Device 100 is not so limited, however, and instead can be constructed from other material(s). In so selectively organizing and sizing sections 110, 120, 130, device 100 is configured to capture different clot types. In some examples, the outer diameter of section 130 can be sized as big as the diameter of vessel in which it is delivered to capture any fragments easily and avoid distal embolization. The outer diameter of section 120 can be relatively smaller while the outer diameter of section 110 can be even smaller to capture larger clots more easily (e.g., fibrin rich clots). Advantageously, the smaller diameter of section 110 can prevent blood vessel damage if the clot is fibrin rich and/or if it rolls over during retrieval. In some examples, section 110 can be beneficial in clot retention within device 100.

In some examples, varying diameters of sections 110, 120, 130 facilitates as described and shown can be particularly advantageous in capturing clot fragments during use that can be missed by section 110 since sections 120, 130 gradually increasing in diameter can securely capture fragments from the friable part of the clot. Sections 110, 120, 130 can be particularly advantageous in minimizing risk of damage to the vessel wall during clot retrieval. For example, if the clot is relatively large, the correspondingly small diameter of device 100 can allow space for the big clots and in turn minimize or reduce friction between the clot and the vessel wall during clot removal. Device 1 can also facilitate clot capture if the clot rolls over during use of device 100 or if the clot changes shape during retrieval.

Further, the outer diameters of section 110, 120, and 130 can otherwise vary and/or be substantially similar. For example, section 120 can include an inner member 103 while section 130 may not necessarily include any inner member 103 and instead include a substantially open distal end terminating in one or more distal crowns or apexes 136 not connected to any cell or element of section 130. Likewise, sections 110 and 120 can each include a substantially open distal end terminating in one or more distal crowns or apexes 116, 126, respectively, not connected to any cell or element of respective sections 110, 120.

Section 130 can be configured to include one or more struts configured to pinch clot C. In some examples, the pinch of section 130 can be achieved by forwarding a microcatheter or intermediate catheter over the device until a portion of clot is compressed between the tip of the catheter and a crown or strut of section 130 (e.g., apex 136). The diameter of section 130 can vary up to approximately 150% of the diameter of blood vessel BV at clot C. For example, the microcatheter can be forwarded distally to pinch a portion of the clot between the tip of the microcatheter and section 130 adjacent to the low radial force area. Section 130 distal of sections 110, 120 provides additional grip and control of the distal end of clot C during dislodgement and retention. Strut members and corresponding cells of section 130 can include a variety of shapes and designs configured for pinching fibrin rich clots, including those described in U.S. Pat. Nos. 10,292,723; 10,363,054; U.S. application Ser. No. 15/359,943; U.S. application Ser. No. 16/021,505; and U.S. application Ser. No. 16/330,703, each of which are incorporated by reference in their entirety as if set forth verbatim herein.

Compression of the clot by section 130 and/or the one or more cells 150 of this disclosure can alter the clot properties and make the clot less amenable to retrieval by making it firmer and “stickier” as described in WO2012/120490A, the entire contents of which are herein incorporated by reference. The device 100 of this disclosure is intended to facilitate clot retrieval by expanding between the clot and the vessel wall in such a way as to engage with the clot over a surface area and do so with minimal compression of the clot. In some examples, the pinch can be achieved by forwarding a microcatheter or intermediate catheter over the device until a portion of clot is compressed between the catheter and cell 150 or section 130. However, actuation of the respective cell 150 or section 130 is not so limited and can be also carried out by pulling one or more pull members attached therewith, by delivering a current to one or more of strut members of respective cell 150 or section 130 to cause to change from a collapsed configuration to pinch configuration, and/or the like. This pinch facilitates removal of the clot as it increases the grip of the device on the clot, particularly fibrin rich clots. It may also elongate the clot reducing the dislodgement force by pulling the clot away from the vessel wall during the dislodgement process.

The segmented and hinged design of cells 150 between sections 110, 120, 130 is also specifically tailored to achieving apposition in bends in the vasculature. The only connecting members of device 100 are cells 150 which function as hinge elements configured to self-align to the neutral axis and allow the device to easily articulate in the bend. In some examples, each of members 103 and cells 150 shown in FIG. 1 be laser cut from a single microtube having an outer diameter smaller than the inner diameter of the collapsed outer member when said outer member is loaded in a microcatheter. The opening angles of the cells of the inner tube are configured so that the change in length (or foreshortening) of the inner tube as it moves from the collapsed to expanded configuration is similar to that of the outer member, thus facilitating a connection between the distal ends of both inner and outer members.

A range of designs are envisaged for each of these elements as described throughout this document, and it is intended that any of these elements could be used in conjunction with any other element, although to avoid repetition they are not shown in every possible combination. Sections 110, 120, 130 are desirably made from a material capable of recovering its shape automatically once released from a highly strained delivery configuration. A superelastic material such as Nitinol or an alloy of similar properties is particularly suitable. The material could be in many forms such as wire or strip or sheet or tube. A particularly suitable manufacturing process is to laser cut a Nitinol tube and then heat set and electropolish the resultant structure to create a framework of struts and connecting elements. This framework can be any of huge range of shapes as disclosed herein and may be rendered visible under fluoroscopy through the addition of alloying elements (e.g., Platinum) or through a variety of other coatings or marker bands.

FIG. 2A depicts a close-up view of an example pinching cell 250, which is similar to cell 150 of device 100. Each of cells 250 can be configured embed and/or engage with and grip the clot to retain it securely for retraction. It is understood that each of the herein described pinching cells can be used interchangeably with clot retrieval devices as needed or required. Cell 250 can include a proximal end 204 and a distal end 208 between which strut members 212 a, 212, 212 c and 212 d are positioned. One or more of strut members 212 a, 212 b, 212 c and 212 d can be configured as bowed or otherwise including tensioned flex so as to be capable of embedding in a clot and then being actuated by gripping or pinching the clot during use. Cells 250 can be actuated into the pinch configuration by being unsheathed from a sheath (e.g., a microcatheter), by being pulled or actuated by one or more pull members, delivering a current to one or more of strut members 212 a, 212, 212 c and 212 d to cause at least a first portion of the one or more of strut members 212 a, 212, 212 c and 212 d to change from a collapsed configuration to pinch configuration.

The diameter of cell 250 can range between approximately 2-10 millimeters depending on how much the design profile allows. One preferred diameter can be approximately 2.25 millimeters. In some examples, cells 250 can be small enough to fit in a 0.021 or 0.018 inch ID microcatheter.

FIG. 2B depicts a close-up view of another example pinching cell 250′ with strut members 212 a′, 212 b′, and 212 c′ now shown with undulating edges. These undulations can be formed by being heat-set, crimped, or otherwise formed as needed or required. FIG. 2C depicts a close-up view of another example pinching cell 250″ with strut members 212 a″, 212 b″, and 212 c″ each including one or more eyelets.

FIG. 3B depicts a close-up view of another example pinching cell 350 with strut members 312 a, 312 b, and 312 c now shown with relatively straight, non-curved strut members interconnected between ends 304, 308. These undulations can be formed by being heat-set, crimped, or otherwise formed as needed or required. FIG. 3C depicts a close-up view of another example pinching cell 350′ with strut members 312 a′, 312 b′, and 312 c′ each including one or more notches or indentation.

Turning back to device 100, FIG. 4 depicts a side view of device 100 in an example blood vessel BV in use with an example clot C whereby device 100 is shown in the initial clot position engaged with clot C at section 110. Section 120 distal thereof is engaged as clot C can roll over and fragment, whereby fragments of clot C are shown captured by section 130. Device 100 of FIG. 4 also includes a first pinching cell 150 proximal of section 110, a second pinching cell 150 between sections 110, 120 and a third pinching cell 150 between sections 120, 130. Each cell 150 provides enhanced grip of the clot C, and any fragments thereof. Each of cells 150 can be particularly advantageous in capturing clots which may have fibrin core in the center, distal or proximal location in the clot C. Moreover, in use, if grip on some of a clot C is missed by one cell 150, one or more cells 150 distal thereof can engage and/or grip the clot C.

FIG. 5A depicts a side view of device 100 in blood vessel BV in use with clot C after the step shown in FIG. 4 . As shown, clot C is engaged between and/or with sections 110, 120 so that device 100 is clearly configured to capture both fibrin rich and friable red blood cell rich clots. the overall device design will help to easily capture fibrin rich and red blood cell rich clots. The three pinch segments will help to capture a clot where the fibrin rich core may be located anywhere in the clot. The increasing diameter of the device will help to reduce clot fragmentation. Between sections 110, 120, cell 150 has also engaged clot C. In FIG. 5B, device 100 is sheathed by microcatheter 70 to cause cells 150 to grip and/or pinch the clot C tightly by pulling cells 150 inside the microcatheter 70 until resistance is felt, which would symbolize that the clot is gripped tightly within cells 150. Clot C can be secured by aspiration via microcatheter 70.

FIG. 6A depicts a side view of device 100 in another example blood vessel BV with an example clot C. FIG. 6B depicts a side view of device 100 of FIG. 6A after actuation of a tilt feature associated with one or more distal crowns or apexes 116′, 126′. Device 100 of FIGS. 6A-6B is particularly useful in capturing clots at vasculature bifurcations which are difficult to remove with one stentriever device of existing technologies. For purposes of this application, if a clot is present in two different branches of the blood vessel BV (e.g., M1 and M2), the blood vessel BV is referred as a “major blood vessel” and the other branches with the clot but no stentriever are referred to as “minor blood vessels.” Through the tilt features of the one or more distal crowns or apexes 116′, 126′ of sections 110, 120, the outer cages are configured to open-up around bifurcations. When the one or more distal crowns or apexes 116′, 126′ of sections 110, 120 are angled as shown between FIGS. 6A-6B, the outer cage of each respective section 110, 120, can open up like a flower (e.g., by pivoting about one or more strut joints, junctions, or hinge elements as denoted in FIG. 6A with the large rotational arrow) and expand causing struts associated respective distal crowns or apexes 116′, 126′ in the bifurcations to capture clot.

Moreover, these tilt features of the one or more distal crowns or apexes 116′, 126′ of sections 110, 120 can cause an increase in outer diameter of sections 110, 120 that enhances grip of the clot C even at the bifurcation as the clot C is gripped between the inner and the outer cages of sections 110, 120. When the clot is present at the bifurcation, the three pinch features can facilitate clot grip and/or pinch in each different branches of the blood vessels. The gradual increasing diameter of the outer cage between sections 110, 120, 130 and respective inner segments (e.g., member 103, cells 150, etc.) can keep the clot C retained inside the vessel BV. Re-sheathing of device 100 with microcatheter 70, as well as aspiration therethrough, can also enhance device 100's grip of the clot C present at the bifurcations.

Turning to FIG. 7A, device 100′ is shown, which is similar to device 100. Device 100′ includes five (5) sequentially positioned hinge elements, pinching cells 150, including at least one with sections 110 and 120. Outer diameters of sections 110, 120, and 130, similar to device 100, generally increase from smallest at section 110 to largest at section 130. Although not shown, an inner body 103 with corresponding flow channel may be included with at least one of sections 110, 120, similar to device 100. Arranging cells 150 as shown can ease manufacturing as well as enhance gripping the clot via the additional cells 150. Increasing diameter between sections 110, 120, and 130 can prevent clot fragmentation.

Turning to FIG. 7B, device 100″ is shown, which is similar to device 100′ with the main difference being all three sections 110″, 120″, 130″ have approximately the same diameters. Either of devices 100, 100′, and 100″ from a single tube for of a memory alloy (e.g., Nitinol) as to the inner segment (e.g., cells 150, inner body 103, etc.) and a single tube of memory alloy can similarly be used to manufacture the outer tube corresponding to sections 110, 120, 130. In some examples, relatively small gaps can be provided between sections 110, 120 and cells 150 to create a clot inlet mouth and expose cells 150 to the clot(s).

FIG. 8 is a flow diagram illustrating a method of removing a clot from a blood vessel of a patient, according to aspects of the present disclosure. The method steps in FIG. 8 can be implemented by any of the example means described herein or by similar means, as will be appreciated. Referring to method 8000 as outlined in FIG. 8 , in step 8010, delivering a clot removal device in a blood vessel at or adjacent a site of a clot, the clot removal device comprising a collapsed state and an expanded state and including a first scaffolding section, a second scaffolding section distal of the first scaffolding section by a first hinged element comprising a pinching cell comprising a collapsed state and an expanded state configured to pinch at least a portion of a clot, and a third scaffolding section distal of the second scaffolding section by a second hinged strut element comprising a pinching cell comprising a collapsed state and an expanded state configured to pinch at least a portion of the clot. In step 8020, method 8000 includes embedding at least one of cells and scaffolding sections with at least a portion of the clot in a clot reception space by expanding the clot removal device from the collapsed state to the expanded state. In step 8030, method 8000 includes removing at least a portion of the clot by withdrawing the clot removal device. Method 8000 can end after step 8030. In other embodiments, additional steps according to the examples described above can be performed.

The disclosure is not limited to the examples described, which can be varied in construction and detail. The terms “distal” and “proximal” are used throughout the preceding description and are meant to refer to a positions and directions relative to a treating physician. As such, “distal” or distally” refer to a position distant to or a direction away from the physician. Similarly, “proximal” or “proximally” refer to a position near to or a direction towards the physician.

In describing examples, terminology is resorted to for the sake of clarity. It is intended that each term contemplates its broadest meaning as understood by those skilled in the art and includes all technical equivalents that operate in a similar manner to accomplish a similar purpose. It is also to be understood that the mention of one or more steps of a method does not preclude the presence of additional method steps or intervening method steps between those steps expressly identified. Steps of a method can be performed in a different order than those described herein without departing from the scope of the disclosed technology. Similarly, it is also to be understood that the mention of one or more components in a device or system does not preclude the presence of additional components or intervening components between those components expressly identified.

As discussed herein, a “patient” or “subject” can be a human or any animal. It should be appreciated that an animal can be a variety of any applicable type, including, but not limited to, mammal, veterinarian animal, livestock animal or pet-type animal, etc. As an example, the animal can be a laboratory animal specifically selected to have certain characteristics similar to a human (e.g., rat, dog, pig, monkey, or the like).

As used herein, the terms “about” or “approximately” for any numerical values or ranges indicate a suitable dimensional tolerance that allows the part or collection of components to function for its intended purpose as described herein. More specifically, “about” or “approximately” may refer to the range of values ±20% of the recited value, e.g. “about 90%” may refer to the range of values from 71% to 99%.

By “comprising” or “containing” or “including” is meant that at least the named compound, element, particle, or method step is present in the composition or article or method, but does not exclude the presence of other compounds, materials, particles, method steps, even if the other such compounds, material, particles, method steps have the same function as what is named.

It must also be noted that, as used in the specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. Ranges can be expressed herein as from “about” or “approximately” one particular value and/or to “about” or “approximately” another particular value. When such a range is expressed, other exemplary embodiments include from the one particular value and/or to the other particular value.

The descriptions contained herein are examples of the disclosure and are not intended in any way to limit the scope of the disclosure. While particular examples of the present disclosure are described, various modifications to devices and methods can be made without departing from the scope and spirit of the disclosure. For example, while the examples described herein refer to particular components, the disclosure includes other examples utilizing various combinations of components to achieve a described functionality, utilizing alternative materials to achieve a described functionality, combining components from the various examples, combining components from the various example with known components, etc. The disclosure contemplates substitutions of component parts illustrated herein with other well-known and commercially-available products. To those having ordinary skill in the art to which this disclosure relates, these modifications are often apparent and are intended to be within the scope of the claims which follow. 

What is claimed is:
 1. A clot removal device, comprising: a first scaffolding section comprising a first pinching cell; a second scaffolding section distal of the first scaffolding section and directly connected to the first scaffolding section by a first hinged element comprising a second pinching cell comprising three or more strut members, wherein at least two of the three or more strut members of the second pinching cell comprise at least one eyelet element configurable in a collapsed state or an expanded state to pinch at least a portion of a clot; a third scaffolding section distal of the second scaffolding section and directly connected to the second scaffolding section by a second hinged element comprising a third pinching cell comprising a collapsed state and an expanded state configured to pinch the at least a portion of the clot, wherein at least two of three or more strut members of the third pinching cell comprises at least one eyelet element configurable in a collapsed state or an expanded state to pinch the at least a portion of the clot; and an outer diameter of the third scaffolding section being greater than an outer diameter of the second scaffolding section which is greater than an outer diameter of the first scaffolding section; wherein the first hinged element has a proximal end and a distal end between which the second pinching cell is positioned, each of the at least two of the three or more strut members of the second pinching cell comprises the at least one eyelet element configurable in the collapsed state or the expanded state to pinch the at least a portion of the clot, wherein the proximal end of the first hinged element comprises a single proximal strut connected to the first scaffolding segment section and the distal end of the first hinged element comprises a single distal strut connected to the second scaffolding segment section, each of the at least two of the three or more strut members of the second pinching cell has a proximal end connected to the single proximal strut, each of the at least two of the three or more strut members of the second pinching cell has a distal end connected to the single distal strut; each of the at least two of the three or more strut members of the second pinching cell is comprised of a single strut, each of the single struts has the at least one eyelet disposed thereon spaced from and between the strut proximal end and the strut distal end.
 2. The clot removal device of claim 1, further comprising: a hinged element comprising a pinching cell proximal of the first scaffolding section and connected to a distal end of a shaft.
 3. The clot removal device of claim 2, wherein at least one of three or more strut members of the first pinching cell further comprise a sinusoidal or notched strut pattern.
 4. The clot removal device of claim 1, the first scaffolding section extended at least partially over an inner body comprising a flow channel configured to engage the clot and restore blood flow through the clot, the inner body comprising a collapsed state and an expanded state; the outer diameters of the first scaffolding section and second scaffolding section being greater than an outer diameter of the inner body in the expanded state to define a clot reception space between the inner body and the separate first and second scaffolding sections, the device further comprising: a first clot inlet mouth between the first and second scaffolding section.
 5. The clot removal device of claim 4, each hinged element configured to self-align the corresponding scaffolding sections to articulate in bends of the vasculature, the second scaffolding section extended at least partially over an inner body comprising a flow channel configured to engage the clot and restore blood flow through the clot, the inner body of the second scaffolding section comprising a collapsed state and an expanded state; each hinged element being the only point of contact between respective clot scaffolding sections.
 6. The clot removal device of claim 5, a proximal end of each respective flow channel joined at a respective proximal end of a respective scaffolding section and a distal end of each respective flow channel joined at a respective a subsequent scaffolding section.
 7. The clot removal device of claim 4, each of the first, second, and third scaffolding sections comprising an open distal end, each of the first, second, and third scaffolding sections comprise a plurality struts formed of closed cells, the distal end of at least one of the first, second, and third scaffolding sections terminates in at least one distal apex free from connection to an adjacent closed cell of the respective scaffolding sections.
 8. The clot removal device of claim 7, the at least one distal apex being a petal or leaf member configured to open up in a flower-like manner and expand in one or more bifurcations of the vasculature to remove the clot.
 9. The clot removal device of 4, each of the first, second, and third scaffolding sections comprising an open distal end, each of the first, second, and third scaffolding sections comprise a plurality struts formed of closed cells, the distal end of at least one of the first, second, and third scaffolding sections terminating in crowns with no distal connecting elements, at least one of the crowns configured to pivot open in a flower-like manner as clot engages therewith.
 10. The clot removal device of claim 4, wherein the device is configured so that expanding the clot removal device causes at least one of the pinching cells, the first scaffolding section, the second scaffolding section, and the third scaffolding section to deform the at least a portion of the clot.
 11. The clot removal device of claim 1, a ratio of a diameter of each pinching cell between the collapsed state and a clot pinching state of the expanded state is from approximately 1.5:1 to 4:1.
 12. The clot removal device of claim 1, the third scaffolding section comprising a constrained delivery configuration and an at least partially constrained clot pinching configuration, at least a portion of the third scaffolding section being configured to engage the clot in the expanded state and to pinch the clot on movement from the expanded state to the clot pinching configuration.
 13. The clot removal device of claim 12, the third scaffolding section comprises a clot pinching structure configured to pinch the clot on movement from the expanded state to the clot pinching configuration.
 14. The clot removal device of claim 1, the third scaffolding section being configured to exert an outward radial force when deployed within a lumen whose inner diameter is lower than that of the expanded state, the outward radial force varying in a generally sinusoidal pattern along a length of the third scaffolding section, the generally sinusoidal pattern comprising a wave pattern and the amplitude generally consistent along the length.
 15. The clot removal device of claim 1, at least five (5) pinching cells being positioned end-to-end between proximal and distal ends of the device.
 16. The clot removal device of claim 1, wherein the second hinged element has a proximal end and a distal end between which the third pinching cell is positioned, each of the at least two of the three or more strut members of the third pinching cell comprises the at least one eyelet element configurable in the collapsed state or the expanded state to pinch the at least a portion of the clot, wherein the proximal end of the second hinged element comprises a single proximal strut connected to the second scaffolding segment and the distal end of the second hinged element comprises a single distal strut connected to the third scaffolding segment , each of the at least two of the three or more strut members of the third pinching cell has a proximal end connected to the single proximal strut, each of the at least two of the three or more strut members of the third pinching cell has a distal end connected to the single distal strut; each of the at least two of the three or more strut members of the third pinching cell is comprised of a single strut, each of the single struts has the at least one eyelet disposed thereon spaced from and between the strut proximal end and the strut distal end, the at least one eyelet having a first curved portion and a second curved portion, each of the first curved portion and the second curved portion having a proximal end and a distal end, the proximal end of the first curved portion is connected to the proximal end of the second curved portion and the distal end of the first curved portion is connected to the distal end of the second curved portion.
 17. The clot removal device of claim 1, wherein the at least one eyelet of each of the at least two of the three strut members of the second pinching cell has a first curved portion and a second curved portion, each of the first curved portion and the second curved portion having a proximal end and a distal end, the proximal end of the first curved portion is connected to the proximal end of the second curved portion and the distal end of the first curved portion is connected to the distal end of the second curved portion. 